CN117157012A

CN117157012A - Optical ultrasonic integrated endoscope probe based on transparent ultrasonic sensor, endoscope equipment and catheter equipment

Info

Publication number: CN117157012A
Application number: CN202180096930.XA
Authority: CN
Inventors: 金哲弘; 金亨咸; 朴正愚; 赵圣熙; 金宰佑; 许多松; 朴馠离
Original assignee: Posco Co Ltd; Academy Industry Foundation of POSTECH
Current assignee: Academy Industry Foundation of POSTECH; Posco Holdings Inc
Priority date: 2021-04-13
Filing date: 2021-10-18
Publication date: 2023-12-01
Also published as: KR20220141507A; US20240164752A1; WO2022220350A1; EP4324401A1; JP2024512991A

Abstract

An optical ultrasonic integrated endoscope probe based on a transparent ultrasonic sensor according to an embodiment of the present invention may include: a fiber laser unit for emitting light; a transparent ultrasonic sensor disposed between an object to be measured and the fiber laser unit so that light emitted from the fiber laser unit is transmitted through the transparent ultrasonic sensor, the transparent ultrasonic sensor being coaxially aligned with the light emitted from the fiber laser unit, radiating ultrasonic waves to the object, and receiving the reflected ultrasonic waves; and an imaging device for acquiring an image of the object through the transparent ultrasonic sensor. An optical ultrasound integrated endoscopic device based on a transparent ultrasound sensor according to an embodiment of the present invention may include the probe, scanning unit and front end unit described. An optical ultrasonic integrated catheter device based on a transparent ultrasonic sensor according to an embodiment of the present invention may include: a fiber laser unit for emitting light from the front end unit; a catheter including a transparent ultrasonic sensor disposed between an object to be measured and the fiber laser unit such that light emitted from the fiber laser unit is transmitted through the transparent ultrasonic sensor, the transparent ultrasonic sensor being coaxially aligned with the light emitted from the fiber laser unit, radiating ultrasonic waves to the object, receiving the reflected ultrasonic waves, and transmitting the received ultrasonic waves to the front end unit; a scanning unit; a front end unit.

Description

Optical ultrasonic integrated endoscope probe based on transparent ultrasonic sensor, endoscope equipment and catheter equipment

Technical Field

The present disclosure relates to an optical ultrasound integrated endoscope probe, an endoscope apparatus, and a catheter apparatus based on a transparent ultrasound sensor.

Background

Ultrasonic sensors or transducers are sensors capable of physical distance measurement and object image acquisition from an object based on the principle of using the characteristics of a piezoelectric material to convert electrical energy into acoustic energy, transferring the acoustic energy to a target object, and then converting the reflected acoustic energy back into an electrical signal.

Recently, for high-precision sensing operation, high-resolution imaging, and user convenience, a technology of integrating optical devices (such as an optical imaging apparatus and a laser) with an ultrasonic sensor is actively being developed.

In particular, since it has an advantage of improving accuracy in medical diagnosis, studies have been made of integrating a conventional ultrasonic imaging system and an optical imaging system, integrating an ultrasonic imaging system and an optical coherence tomography system, integrating an ultrasonic imaging system and a fluorescence imaging system, and the like.

However, since the conventional ultrasonic sensor is opaque, the ultrasonic sensor cannot be integrated with an optical device requiring a transparent medium, and cannot be arranged on the same axis as the irradiated laser light.

Such an off-axis arrangement is disadvantageous in capturing images for various reasons. For example, problems such as misalignment of the system, increased complexity, increased system size, and reduced signal-to-noise ratio (SNR) occur.

To solve the problem of such an opaque ultrasonic sensor, U.S. patent No. 8,784,321 discloses that a portion of the end surface of the opaque ultrasonic sensor is penetrated to form an optical path such that the optical path and the ultrasonic path are arranged on the same axis. However, even in this case, since light may transmit only a part of the end surface of the ultrasonic sensor, the problem caused by the light non-transmittance of the ultrasonic sensor may not be sufficiently solved.

Meanwhile, the present inventors have filed korean patent application No. 10-2020-0039208 ("transparent ultrasonic sensor and method for manufacturing the same") that discloses a single crystal transparent ultrasonic sensor structure based on Lithium Niobate (LNO) and korean patent application No. 10-2020-0117777 ("ultra sonic-optical multiimaging system based on transparent ultrasonic sensor") that discloses an ultrasonic optical multi-imaging system using a transparent ultrasonic sensor.

(patent document 1) U.S. patent publication No. 8,784,321

(patent document 2) Korean patent application No. 10-2020-0039208

(patent document 3) Korean patent application No. 10-2020-0117777

Disclosure of Invention

Technical problem

The present disclosure provides an optical ultrasonic integrated endoscope probe, an endoscope apparatus, and a catheter apparatus based on a transparent ultrasonic sensor, which can improve SNR and miniaturize the apparatus by using the transparent ultrasonic sensor that coaxially aligns an ultrasonic path and an optical path.

Technical proposal

In one aspect of the present invention, an optical ultrasound integrated endoscope probe based on a transparent ultrasound sensor may include: a fiber laser unit emitting light; a transparent ultrasonic sensor disposed between an object to be measured and the fiber laser unit so that light emitted from the fiber laser unit is transmitted through the transparent ultrasonic sensor, the transparent ultrasonic sensor being coaxially aligned with the light emitted from the fiber laser unit, radiating ultrasonic waves to the object, and receiving the reflected ultrasonic waves; and an imaging device that acquires an image of the object through the transparent ultrasonic sensor. In another aspect of the present invention, an optical ultrasonic integrated endoscope apparatus based on a transparent ultrasonic sensor may include: a probe; a scanning unit connected to the probe through a cable to control a scanning operation of the probe; and a front end unit that provides an optical output to the probe through the cable and performs signal processing on an image acquired by the probe. In another aspect of the invention, an optical ultrasound integrated catheter device based on a transparent ultrasound sensor may comprise: a catheter inserted into a predetermined object; a scanning unit connected to the catheter through a cable to control a scanning operation of the catheter; and a front end unit providing an optical output to the catheter through a cable and performing signal processing on an image acquired by the catheter, wherein the catheter may include: a fiber laser unit that emits light from the front end unit; and a transparent ultrasonic sensor disposed between the object to be measured and the fiber laser unit such that light emitted from the fiber laser unit is transmitted through the transparent ultrasonic sensor, the transparent ultrasonic sensor being coaxially aligned with the light emitted from the fiber laser unit, radiating ultrasonic waves to the object, and receiving the reflected ultrasonic waves and transmitting the received reflected ultrasonic waves to the front end unit.

Advantageous effects

According to the embodiments of the present disclosure, by using a transparent ultrasonic sensor capable of achieving coaxialization of an ultrasonic path and an optical path, SNR can be improved and a probe or catheter can be miniaturized.

Drawings

Fig. 1 is a schematic configuration diagram of a transparent ultrasonic sensor-based optical ultrasonic integrated endoscope apparatus or catheter apparatus according to an embodiment of the present disclosure.

Fig. 2 is a schematic front perspective view of a transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe according to an embodiment of the present disclosure.

Fig. 3 a-3 d are schematic front perspective views of transparent ultrasonic sensor-based optical ultrasonic integrated endoscopic probes in accordance with various embodiments of the present disclosure.

Fig. 4 a-4 c are schematic configuration diagrams of a front-view transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe or catheter according to various embodiments of the present disclosure.

Fig. 5 a-5 c are schematic configuration diagrams of a transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe or catheter in which a reflector is added to a forward-looking probe or catheter, according to various embodiments of the present disclosure.

Fig. 6 a-6 i are schematic configuration diagrams of a transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe or catheter, with reflectors added to the side-view probe or catheter, according to various embodiments of the present disclosure.

Fig. 7a to 7d are diagrams illustrating embodiments of reflectors employed in a transparent ultrasonic sensor-based optical ultrasonic integrated endoscope apparatus or a catheter apparatus, respectively, according to embodiments of the present disclosure.

Fig. 8 is a schematic configuration diagram of a transparent ultrasonic sensor-based optical ultrasonic integrated endoscope apparatus or catheter apparatus according to another embodiment of the present disclosure.

Fig. 9a is a front view of a transparent ultrasonic sensor employed in a transparent ultrasonic sensor-based optical ultrasonic integrated endoscope apparatus or catheter apparatus according to an embodiment of the present disclosure, and fig. 9b is a rear view of the transparent ultrasonic sensor according to an embodiment of the present disclosure.

Fig. 10 is a schematic unidirectional cross-sectional view of a transparent ultrasonic sensor employed in a transparent ultrasonic sensor-based optical ultrasonic integrated endoscopic device or catheter device in accordance with an embodiment of the present disclosure.

Fig. 11 is a schematic exploded perspective view of a transparent ultrasonic sensor employed in a transparent ultrasonic sensor-based optical ultrasonic integrated endoscope apparatus or catheter apparatus according to an embodiment of the present disclosure.

Fig. 12a and 12b are diagrams showing light path examples when a plano-concave acoustic lens and a plano-convex acoustic lens are used in a transparent ultrasonic sensor employed in a transparent ultrasonic integrated endoscope apparatus or a catheter apparatus based on the transparent ultrasonic sensor according to an embodiment of the present disclosure, respectively.

Fig. 13a and 13b are diagrams showing examples of optical paths when a correction lens is used and a correction lens is not used in a transparent ultrasonic sensor employed in a transparent ultrasonic integrated endoscope apparatus or a catheter apparatus based on the transparent ultrasonic sensor according to an embodiment of the present disclosure, respectively.

Fig. 14 and 15 are graphs showing photoacoustic image results obtained by the transparent ultrasonic sensor-based optical ultrasonic integrated catheter apparatus according to the embodiment of the present disclosure.

Detailed Description

Hereinafter, embodiments will be described in detail with reference to the drawings so as to be easily practiced by those skilled in the art to which the present disclosure pertains.

Referring to fig. 1, a transparent ultrasonic sensor-based optical ultrasonic integrated endoscope apparatus or catheter apparatus 100 according to an embodiment of the present disclosure may include an endoscope probe or catheter 110, an operation unit 120, and a front end unit 130.

The endoscope probe or catheter 110 may be inserted into a preset object to acquire an ultrasonic image, a photoacoustic image, or the like of the object to be captured. As described above, the endoscope probe or catheter 110 may be inserted into a preset object to acquire an ultrasonic image, a photoacoustic image, or the like of the object to be captured. For example, in the case of an endoscope probe inserted into a body organ such as the stomach and large intestine, the outer diameter of the endoscope probe may be about 5mm to 15mm, and in the case of a catheter inserted into a stenotic site such as a cardiovascular, microvascular, or the like, the outer diameter of the catheter may be about 0.5mm to 1mm.

The operation unit 120 may control the movement of the endoscope probe or the catheter 110 connected through a cable. The operation unit 120 may include a knob unit 121, an intake valve 122, an air/water valve 123, and an instrument port 124.

The knob unit 121 may control movement of the endoscope probe or the guide tube 110 according to a user's operation, the suction valve 122 may control a suction operation of a suction unit installed in the endoscope probe or the guide tube 110 described later, the air/water valve 123 may control an operation of a water nozzle device installed in the endoscope probe or the guide tube 110 described later, and the instrument port 124 may control operation of the medical device through a forceps hole installed in the endoscope probe or the guide tube 110 described later.

The front-end unit 130 may include a signal processing unit 132, the signal processing unit 132 transmitting an ultrasonic signal to the endoscope probe or catheter 110 through a laser light source 131, receiving and signal-processing the reflected ultrasonic signal, and signal-processing and displaying an acquired photoacoustic image or the like, the laser light source 131 providing laser light through a fiber optic cable and a signal line.

Referring to fig. 2 and 1, a transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe 110 according to an embodiment of the present disclosure includes an ultrasonic sensor 111, a fiber laser unit 112, and an image pickup device 113.

The fiber laser unit 112 may receive laser light from the laser light source 131 of the front end unit 130 and emit light to the outside of the probe 110. The fiber laser unit 112 may be a laser device of various wavelengths for photoacoustic, OCT, near infrared fluorescence (NIRF), near infrared spectroscopy (NIRS), and fluorescence imaging. The fiber laser unit 112 may be a small image pickup device (CCD, CMOS sensor), LED, or the like, in addition to a laser. Although only one fiber laser unit 112 is shown, a plurality of fiber laser units 112 may be arranged within a limited size to simultaneously acquire a plurality of optical images.

The transparent ultrasonic sensor 111 may be disposed between an object to be measured and the fiber laser unit 112 and coaxially aligned with light emitted from the fiber laser unit 112, may transmit light emitted from the fiber laser unit 112, be connected to the signal processing unit 132 of the front end unit 130 through a signal line to radiate ultrasonic waves to the object, and receive the reflected ultrasonic waves to acquire an ultrasonic image. The image pickup device 113 may be connected to the signal processing unit 132 of the front end unit 130 through a signal line to acquire an image of an object through the transparent ultrasonic sensor 111, and may transmit the acquired image to the signal processing unit 132.

As described above, the optical ultrasonic integrated endoscope probe 110 based on the transparent ultrasonic sensor according to the embodiment of the present disclosure transmits light from the fiber laser unit 112 to the rear surface of the transparent ultrasonic sensor 111 to acquire an optical/ultrasonic image or signal at the same position as the light and the ultrasonic wave, reduces the volume of the apparatus and increases the number of forceps holes in the additional portion of the apparatus to add various surgical tools and the like, and overcomes the problem of positional inconsistency between the conventional ultrasonic image and the optical image because the ultrasonic waves/light can completely share the same positional information.

Fig. 3 a-3 d are schematic front perspective views of transparent ultrasonic sensor-based optical ultrasonic integrated endoscopic probes according to embodiments of the present disclosure.

Referring to fig. 3a to 3d and 2, the transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe 110 according to various embodiments of the present disclosure may further include a suction unit 114 sucking a preset substance, a forceps hole 115, and a water nozzle device 116 spraying water. As described above, since the volume of the device is reduced, by increasing the number of forceps holes in the additional portion of the device, a plurality of forceps holes 115 performing a preset medical function such as cutting and suturing can be provided.

First, the transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe 110 according to various embodiments of the present disclosure may acquire an ultrasonic image a of an object through the transparent ultrasonic sensor 111 with reference to fig. 3a, acquire an image b of the object through the image pickup device 113 with reference to fig. 3b, acquire photoacoustic images a and c using the fiber laser unit 112 and the transparent ultrasonic sensor 111 with reference to fig. 3c, and acquire a fluorescence image d using the fiber laser unit 112 alone with reference to fig. 3 d.

Meanwhile, except for the configuration in which the above-described image pickup device is excluded from the endoscope probe, the operation and configuration of the catheter employed in the transparent ultrasonic sensor-based optical ultrasonic integrated catheter apparatus 100 according to the embodiment of the present disclosure are similar to those of the endoscope probe, and thus, a detailed description thereof will be omitted.

The transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe or catheter 110 according to various embodiments of the present disclosure may be of the front-view type or of the side-view type.

In the transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe or catheter 110, which will be shown in the drawings described later, the transparent ultrasonic sensor can focus or radiate an ultrasonic signal.

Referring to fig. 4a, in the transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe or catheter 110 according to various embodiments of the present disclosure, a fiber laser unit 112 may be located on a rear surface of a transparent ultrasonic sensor 111, and the transparent ultrasonic sensor 111 transmits/receives ultrasonic waves a from one end to the front to emit light c through the transparent ultrasonic sensor 111.

Referring to fig. 4b, in the transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe or catheter 110 according to various embodiments of the present disclosure, an optical lens 117 may be disposed between the transparent ultrasonic sensor 111 and the fiber laser unit 112 to focus the light c from the fiber laser unit 112. The optical lens 117 may be various, such as a GRIN lens, a ball lens, and a convex lens.

Referring to fig. 4c, in the transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe or catheter 110 according to various embodiments of the present disclosure, a plurality of optical lenses 117 may be arranged between the transparent ultrasonic sensor 111 and the fiber laser unit 112 to adjust a propagation angle or distance of the light c from the fiber laser unit 112. The optical lens 117 at this time may correspond to any lens, diffuser, or the like that can propagate light.

Meanwhile, the transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe or catheter 110 according to various embodiments of the present disclosure may further include a reflector.

Referring to fig. 5a to 5c, the front view type transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe or catheter 110 according to various embodiments of the present disclosure may further include a reflector 118 to transmit/receive ultrasonic waves to a side surface of the transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe or catheter 110 and emit light. Similarly, when an image pickup device (not shown) is included, an image of an object can be acquired. A reflector 118 may be arranged in front of the transparent ultrasonic sensor 111 to change the angle between the ultrasonic waves of the transparent ultrasonic sensor 111 and the light from the fiber laser unit 112.

Referring to fig. 6a to 6i, a side-view transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe or catheter 110 according to various embodiments of the present disclosure may include a fiber laser unit 112, the fiber laser unit 112 being located on a rear surface of a transparent ultrasonic sensor 111, the transparent ultrasonic sensor 111 transmitting/receiving an ultrasonic wave a to emit light c through the transparent ultrasonic sensor 111; and a reflector 118 disposed between the transparent ultrasonic sensor 111 and the fiber laser unit 112 to change an angle of light from the fiber laser unit 112. Further, an optical lens 117 may be disposed between the reflector 118 and the fiber laser unit 112 to focus the light c from the fiber laser unit 112, or a plurality of optical lenses 117 may be disposed to adjust the angle and distance of the light c propagating from the fiber laser unit 112.

Referring to fig. 7a to 7d, various types of reflectors may be used in the transparent ultrasonic sensor-based optical ultrasonic integrated endoscope apparatus or the catheter apparatus according to the embodiment of the present disclosure. Representative examples of the reflector include a mirror, a prism, a beam splitter, a dichroic mirror, and the like, and may include any type of reflector capable of reflecting light or ultrasonic waves.

Referring to fig. 8, in the case of a side-view type probe or catheter, an optical ultrasonic integrated endoscope apparatus or catheter apparatus 200 based on a transparent ultrasonic sensor according to another embodiment of the present disclosure may include an endoscope probe or catheter 210, a scanning unit 220, and a front end unit 230.

The endoscope probe or catheter 210 may be inserted into a preset object to acquire an ultrasonic image, a photoacoustic image, or the like of the object to be captured.

The scanning unit 220 may control the scanning of the endoscope probe or catheter 210 connected by a cable. That is, the scanning unit 220 may rotate the endoscope probe or catheter 210 by 360 ° to control a scanning operation of obtaining an ultrasonic image, a photoacoustic image, or the like of the object.

The scanning unit 220 may include a motor 221, a fiber optic rotary joint unit 222, and a slip ring 223.

The motor 221 may provide torque to rotate the endoscope probe or catheter 210. The fiber optic rotary joint unit 222 may provide coaxial alignment between a fiber optic cable (fiber b) connected to an endoscope probe or catheter (210) rotated according to the torque of the motor 221 and a fiber optic cable (fiber a) connected and fixed to the front end unit 230. The fixed optical fiber cable (optical fiber a) and the optical fiber cable (optical fiber b) rotated by the motor are spaced apart from each other by about several um, laser light may be transmitted from the fixed optical fiber cable (optical fiber a) to the rotated optical fiber cable (optical fiber b) as shown by a dotted line, and the optical fiber rotary joint unit 222 may provide coaxial alignment between the optical fiber cable (optical fiber b) connected to the endoscope probe or catheter 210 rotated according to torque of the motor 221 and the optical fiber cable (optical fiber a) connected to the front end unit 230 and fixed to transmit laser light from the fixed optical fiber cable (optical fiber a) to the rotated optical fiber cable (optical fiber b) as shown by a dotted line. Slip ring 223 may provide an electrical connection between a signal wire (line b) connected to front end unit 230 and fixed, and a signal wire (line b) connected to an endoscopic probe or catheter 110 rotated by motor 221 and rotated.

The front-end unit 230 may include a signal processing unit 232, the signal processing unit 232 transmitting an ultrasonic signal to the endoscope probe or catheter 210 through a laser light source 231, receiving and signal-processing the reflected ultrasonic signal, and signal-processing and displaying an acquired photoacoustic image or the like, the laser light source 231 providing laser light through an optical fiber cable (optical fiber a) and a signal line (line a).

Fig. 9a is a front view of a transparent ultrasonic sensor employed in a transparent ultrasonic sensor-based optical ultrasonic integrated endoscope apparatus or a catheter apparatus according to an embodiment of the present disclosure, fig. 9b is a rear view of a transparent ultrasonic sensor according to an embodiment of the present disclosure, fig. 10 is a schematic unidirectional cross-sectional view of a transparent ultrasonic sensor employed in a transparent ultrasonic sensor-based optical ultrasonic integrated endoscope apparatus or a catheter apparatus according to an embodiment of the present disclosure, and fig. 11 is an exploded perspective view of a transparent ultrasonic sensor employed in a transparent ultrasonic sensor-based optical ultrasonic integrated endoscope apparatus or a catheter apparatus according to an embodiment of the present disclosure.

As shown in fig. 9a and 9b, the transparent ultrasonic sensor 111 according to the embodiment of the present disclosure has a circular shape having a circular planar shape, but is not limited thereto.

Referring to fig. 9a, 9b and 10, the transparent ultrasonic sensor 111 according to the embodiment of the present disclosure may include, from the right side, a protective layer 111-1, a matching unit 111-3 having an acoustic lens located behind the protective layer 111-1, a piezoelectric portion 111-5 located behind the matching unit 111-3, first and second cases 111-7a and 111-7b connected to the piezoelectric portion 111-5, a rear layer 111-6 located behind the piezoelectric portion 111-5, an insulating portion 111-8 located between the first and second cases 111-7a and 111-7b, and a correction lens unit 111-9 located behind the second case 111-7 b.

The protective layer 111-1 serves to physically and electrically protect the transparent ultrasonic sensor 111 and reduce the acoustic impedance difference between media (i.e., objects) to which the ultrasonic signal is to be radiated. Therefore, the protective layer 111-1 has a protective function, and can function as a matching layer that performs acoustic impedance matching between a liquid (e.g., water) and a living body.

The protective layer 111-1 may be made of a transparent substance. For example, the protective layer 111-1 may contain parylene as a transparent polymer.

In this example, the acoustic impedance of the protective layer 111-1 may be about 284 megarayls.

As shown in fig. 10 and 11, the protective layer 111-1 may be located on a side surface of the second case 111-7b, the second case 111-7b is located on a front surface and a side surface of the piezoelectric portion 111-5, and the protective layer 111-1 is located at an outermost edge of the transparent ultrasonic sensor 111.

Thus, the protective layer 111-1 may eventually form the front surface and the side surfaces of the transparent ultrasonic sensor 111.

The matching unit 111-3 located behind the protective layer 111-1 serves to reduce the difference in acoustic impedance between the medium to which the ultrasonic signal generated from the piezoelectric portion 111-5 is to be radiated and the object.

That is, when generating the ultrasonic signal for the operation of the piezoelectric portion 111-5, in order to effectively transmit the ultrasonic signal in water, living tissue, or other medium except air, it is necessary to adjust the acoustic impedance of the medium as much as possible, so that the energy loss of the ultrasonic wave can be minimized.

Each of the acoustic lenses of the matching unit 111-3 of this example may be of a focusing type, using an acoustic lens capable of adjusting the focus of light and ultrasonic signals.

Accordingly, since the matching unit 111-3 has a focus control function, the ultrasonic signal reflected from the object and incident on the transparent ultrasonic sensor 111 is accurately focused on a desired position of the piezoelectric portion 111-5.

Accordingly, by the focus control function of the matching unit 111-3, the focus of the ultrasonic image acquired from the ultrasonic signal output from the piezoelectric section 111-5 can be adjusted to acquire a clear ultrasonic image.

Accordingly, the sharpness of an image obtained by the operation of the transparent ultrasonic sensor 111 is improved, and thus a sharp image of a desired portion of the object to which the ultrasonic signal is irradiated can be obtained.

Further, since the matching unit 111-3 uses an acoustic lens, the curvature of the surface is constant and the transparency of the surface is improved, so that the loss amount of the ultrasonic signal when transmitting or receiving the ultrasonic signal radiated to or reflected from the object can be reduced.

Further, if necessary, an additional transmission film or blocking film may be formed in the matching unit 111-3 to transmit or block only signals of a desired wavelength range.

The acoustic lens provided in the matching unit 111-3 may be made of at least one of transparent glass, transparent epoxy, and transparent silicone.

Such an acoustic lens may be selected according to its function.

For example, in the case where an acoustic lens is used as a matching layer performing an acoustic impedance matching function, the acoustic lens may be more preferably made of glass when the piezoelectric substance provided in the piezoelectric portion 111-5 is not in the form of a polymer such as PVDF or PVDF-TrFE.

That is, when the piezoelectric substance is made of Lithium Niobate (LNO) or PMN-PT, the acoustic impedance is as high as 30 megarayls to 40 megarayls, but when the piezoelectric substance is made of glass, the acoustic impedance is as low as 10 megarayls to 15 megarayls, and thus, an acoustic impedance value that is easily matched with the acoustic impedance is obtained, and also very good transparency is obtained. As a result, when the piezoelectric substance is not in the form of a polymer, the acoustic lens may be made of glass.

However, when a matching layer performing an acoustic impedance matching function has been manufactured, the acoustic lens may be made of transparent epoxy or transparent silicone.

That is, when a matching layer (about 7 to 20 megarayls) performing a matching function between a piezoelectric substance having an acoustic impedance of about 30 to 40 megarayls and living tissue or water having an acoustic impedance of about 1 to 2 megarayls (i.e., a medium to which ultrasonic waves are to be radiated) is pre-existing, epoxy or silicone having an acoustic impedance similar to that of the living tissue or water (about 1 to 3 megarayls) is suitable because a separate acoustic impedance matching operation is not required. That is, since the acoustic impedances of the epoxy resin and the silicone are almost the same as those of the living tissue or water, no separate acoustic impedance matching is required.

Further, the curvature of the curved surface of the acoustic lens and whether the acoustic lens is concave or convex may be determined in consideration of the sound speed and the sound speed of the acoustic lens material.

For example, when the acoustic lens is made of glass, an optical lens may be used. In this case, the light velocity of the glass is faster than that of water, and thus the acoustic lens may be designed to be concave, for example, flat concave (see fig. 12 a).

When the acoustic lens is made of transparent epoxy resin, the acoustic lens produced in the preliminary stage is subjected to polishing treatment to increase transparency as much as possible, thereby finally completing the acoustic lens. Therefore, even when the acoustic lens is made of epoxy resin, the light velocity of the epoxy resin is faster than that of water, and thus the acoustic lens can be manufactured in a flat concave shape.

Even when the acoustic lens is made of transparent silicone, as in the case of epoxy, a separate polishing process should be performed to maximize the finished acoustic lens as much as possible. In this case, since the light velocity of silicone is slower than that of water, the acoustic lens may be manufactured in a convex shape, such as a plano-convex shape, unlike the case of glass and epoxy (see fig. 12 b). Therefore, when the acoustic lens is manufactured in a plano-convex shape, the acoustic lens can have a light condensing function.

As shown in fig. 10 and 11, the piezoelectric portion 111-5 may include a piezoelectric layer 111-5a and first and second electrode layers 111-5b and 111-5c on rear and front surfaces of the piezoelectric layer 111-5a, respectively.

The piezoelectric layer 111-5a is a layer in which a piezoelectric effect and a reverse piezoelectric effect occur, and as described above, may contain a piezoelectric substance that is at least one of Lithium Niobate (LNO), PMN-PT, PVDF, and PVDF-TrFE.

The electromechanical coupling coefficient of the LNO is about 0.49, which is very high, so that the electromechanical energy conversion efficiency is very good.

Further, since the LNO has a low dielectric constant, the use of the transparent ultrasonic sensor can be applied to a large aperture single element transducer when the piezoelectric layer 111-5a is made of LNO.

Further, since the LNO has a high curie temperature and can withstand a high temperature, the transparent ultrasonic sensor 111 having good heat resistance can be developed.

Further, when the piezoelectric layer 111-5a is made of LNO, a single element ultrasonic sensor having a center frequency of 10MHz to 400MHz can be easily developed.

When the piezoelectric layer 111-5a contains PMN-PT, since the piezoelectric properties (d 33 to 1500pC/N to 2800 pC/N) and the electromechanical coupling coefficient (k > 09) of PMN-PT are very high, the performance of the transparent ultrasonic sensor 111 can be improved.

Unlike LNO, PMN-PT has a high dielectric constant, so that a transparent ultrasonic sensor 111 suitable for a small aperture single or array ultrasonic transducer can be developed.

In addition, when the piezoelectric layer 111-5a contains at least one of PVDF and PVDF-TrFE, the piezoelectric layer 111-5a may have the following characteristics.

PVDF and PVDF-TrFE have the form of polymer films and can be used to fabricate the flexible and stretchable piezoelectric layer 111-5a, so the thickness of the piezoelectric layer 111-5a can be reduced and a transparent ultrasonic sensor 111 for a signal of a high frequency band of about 100MHz as the reduced thickness can be fabricated.

In addition, PVDF and PVDF-TrFE can have relatively low electromechanical coupling coefficients and relatively high reception constants, and have a wider bandwidth than other piezoelectric substances, and can be readily used to fabricate a single element or all array elements.

Here, a single element (e.g., a single ultrasonic transducer) may refer to an ultrasonic transducer in which the number of all components including the piezoelectric substance is 1. Furthermore, the array-type element (e.g., an array ultrasonic transducer) may be an ultrasonic transducer having a plurality of components (n) among all components including a piezoelectric substance, and may be generally configured in a form mainly used for hospitals. In this case, the shape may be a linear shape, a convex shape, a 2D matrix, or the like.

In the case of this example, a single or array ultrasonic transducer having a small aperture can be manufactured, similar to PMN-PT.

The material properties of the piezoelectric layer 111-5a can be summarized in the following table.

(watch)

The first electrode layer 111-5b and the second electrode layer 111-5c, which are respectively located on the front and rear surfaces of the piezoelectric layer 111-5a, may respectively receive a (+) driving signal and a (-) driving signal from a driving signal generator (not shown) and apply a reverse piezoelectric effect to the piezoelectric layer 111-5a so that an ultrasonic signal may be transmitted toward the object 200, and conversely, may receive an electrical signal generated through the piezoelectric effect of the piezoelectric layer 111-5a by the ultrasonic signal reflected from the object and output the received electrical signals to the outside.

As described above, the first electrode layer 111-5b and the second electrode layer 111-5c may be made of a transparent conductive substance, and may include at least one of AgNW (silver nanowire), ITO, carbon nanotubes, and graphene, for example.

As shown in fig. 10, in order to be easily coupled with the first and second cases 111-7a and 111-7b, the sizes of the first and second electrode layers 111-5b and 111-5c may be different from each other.

Accordingly, as shown in fig. 10, in the first electrode layer 111-5b and the second electrode layer 111-5c having circular planar shapes, the diameter of the second electrode layer 111-5c is different from that of the first electrode layer, and a portion (e.g., an edge portion) of the second electrode layer 111-5c may protrude outward from the edge portion of the first electrode layer 111-5 b.

When an electrical signal (e.g., a pulse signal) is applied to the piezoelectric substance, the piezoelectric substance (i.e., the piezoelectric layer 111-5 a) vibrates back and forth to generate an ultrasonic signal. The ultrasonic wave signal is generated not only on the front surface of the object-oriented piezoelectric layer 111-5a but also on the rear surface opposite to the front surface.

In this case, since the ultrasonic signal generated on the rear surface is not directed to the object, the ultrasonic signal generated on the rear surface acts as a noise signal.

Further, a part of the ultrasonic signal reflected and returned from the subject may be output through the matching unit 111-5 and toward the correction lens unit 111-9.

Accordingly, the rear layer 111-6 may be positioned on the rear surface of the piezoelectric portion 111-5 to attenuate the ultrasonic signal generated from the rear surface of the piezoelectric portion 111-5 and attenuate the ultrasonic signal reflected from the object.

Therefore, since the rear layer 111-6 is located on the rear surface of the piezoelectric portion 111-5 (that is, the surface opposite to the front surface of the piezoelectric portion 111-5 on which the reflected ultrasonic signal is incident), the ultrasonic signal does not pass through the rear surface of the piezoelectric portion 111-5.

In this way, unnecessary signal interference caused by the ultrasonic signal passing through the rear surface of the piezoelectric portion 111-5 can be prevented, and loss of the ultrasonic signal reflected to the piezoelectric portion 111-5 can be prevented to reduce the ring-down signal, thereby reducing the ring-down phenomenon.

Ring down is a phenomenon in which an unnecessary signal is elongated along a time axis, which is a factor adversely affecting image generation.

Accordingly, the back layer 111-6 can be appropriately manufactured by adjusting at least one of acoustic impedance and thickness so as to reduce such ring-down phenomenon.

When the rear layer 111-6 is made of a substance having a high acoustic impedance, the ring-down phenomenon is reduced, and the reduction of the ring-down phenomenon on the time axis is similar to the meaning of widening the bandwidth in the frequency domain. However, when an ultrasonic signal is transmitted/received instead, the entire size of the ultrasonic signal may also be attenuated by the rear layer 111-6.

In contrast, when the rear layer 111-6 is made of a substance having a relatively low acoustic impedance, the ring-down phenomenon is not significantly reduced and the bandwidth is reduced, but the transmission/reception amount of the ultrasonic signal can be increased.

The back layer 111-6 may also be made of a transparent non-conductive substance and may be made of, for example, a transparent epoxy (e.g., epotek 301) or transparent glass.

When the back layer 111-6 is made of Epotek301 and has an acoustic impedance as low as 31 megarayls, low signal attenuation is achieved, so that a relatively high signal can be obtained by the transparent ultrasonic sensor 111.

In addition, epotek301 has very high transparency, such as transparency of about 95% or more at a wavelength of 380nm to 2000nm, and Epotek301 is easy to manufacture the post-layer 111-6 since Epotek301 is cured at room temperature.

When the rear layer 111-6 is made of glass, the transparency and flatness are high, and a separate curing process is not required.

When the glass has an acoustic impedance of about 13 megarayls, the pulse length is reduced due to high signal attenuation in the back layer 111-6 to reduce the ring down effect, but the effect of increasing the frequency bandwidth of the transparent ultrasonic sensor 111 may be exerted.

The rear layer 111-6 may be omitted if desired.

As described above, the first case 111-7a and the second case 111-7b are connected to the first electrode layer 111-5b and the second electrode layer 111-5c, respectively. Accordingly, the first and second cases 111-7a and 111-7b may be made of a transparent conductive substance containing a conductive substance (e.g., copper) through which an electric signal is transmitted.

Accordingly, as shown in fig. 3, the first housing 111-7a may receive a corresponding signal through the first signal line L1 and transmit the received signal to the first electrode layer 111-5b, and conversely, output a signal applied from the first electrode layer 111-5b to the first signal line L1.

The second case 111-7b may also receive a corresponding signal through a second signal line L2, the second signal line L2 being a different signal line from the first signal line L1, and transmit the received signal to the second electrode layer 111-5c, and conversely, output a signal applied from the second electrode layer 111-5c to the second signal line L2.

In this example, the signal input to the first signal line L1 may be a pulse signal, and the signal introduced to the second signal line L2 may be a ground signal or a shielding signal (-), so the first case 111-7a may transmit the pulse signal to the first electrode layer 111-5b, and the second case 111-7b may transmit the ground signal to the second electrode layer 111-5c.

As shown in fig. 4, the first case 111-7a and the second case 111-7b have a ring shape, and may be positioned to be in contact with edge portions, i.e., circular side surfaces, of the corresponding electrode layers 111-5b and 111-5c.

That is, the first electrode layer 111-5b and the second electrode layer 111-5c may be inserted and mounted into empty spaces inside the first case 111-7a and the second case 111-7 b.

Thus, as shown in fig. 9, the first and second cases 111-7a and 111-7b are positioned such that the transparent ultrasonic sensor 111 encloses the actual effective area AR1, thereby minimizing the reduction of the effective area AR1 by the first and second cases 111-7a and 111-7b (basically the first case 111-7 a).

Accordingly, since the first case 111-7a and the second case 111-7b serve to transmit an electrical signal to the corresponding electrode layers 111-5b and 111-5c, the first case 111-7a and the second case 111-7b may contain a substance having good electrical conductivity.

Since the first case 111-7a is located at an edge portion (i.e., a corner portion) of the first electrode layer 111-5a, the first electrode layer 111-5a is located on the entire rear surface of the piezoelectric layer 111-5a receiving light, the first case 111-7a preferably has a width W11 as thin as possible, and may have a thickness as thick as possible to minimize a loss rate of signals due to wiring resistance or the like.

As shown in fig. 9 and 10, since the second case 111-7b is coupled with the second electrode layer 111-5c having a larger diameter than the first electrode layer 111-5b, the diameter of the second case 111-7b is larger than that of the first case 111-7 a.

In addition, since the second housing 111-7b is more capable of protecting the transparent ultrasonic sensor 111 from the outside than the first housing 111-7a, the width and thickness of the second housing 111-7b may be greater than those of the first housing 111-7 a.

Accordingly, as shown in fig. 10, the first electrode layer 111-5b and the first case 111-7a may be located in the second case 111-7 b.

Further, as described above, the outer side surface of the second housing 111-7b exposed to the outside is covered with the protective layer 111-1, thus preventing noise signals from entering the transparent ultrasonic sensor 111 through the second housing 111-7 b.

As shown in fig. 10 and 11, the second housing 111-7b does not affect the light receiving area of the piezoelectric layer 111-5a, and thus the size can be increased if necessary.

Further, the desired optical element may be coupled to the second housing 111-7b by forming a screw 111-7b1, a connector, or the like on the second housing 111-7b. In this case, the second housing 111-7b may serve as a coupling portion for coupling with other components.

The insulating part 111-8 is located between the first case 111-7a and the second case 111-7b transmitting the corresponding electrical signals to the corresponding electrode layers 111-5b and 111-5c to be in contact with the first case 111-7a and the second case 111-7b, to insulate the first case 111-7a and the second case 111-7b, thereby preventing an electrical short or a short circuit, and may serve to fix the positions of the first case 111-7a and the second case 111-7b.

The insulating portion 111-8 may be made of a transparent insulating substance such as an electrically non-conductive epoxy. As an example of the matching unit 111-3, when a plano-concave acoustic lens is used, the focus of light and ultrasonic signals reflected and incident from the subject is adjusted by the acoustic lens of the matching unit 111-3. However, after the light and ultrasonic signals pass through the matching unit 111-3, a light diffusion phenomenon may occur (see fig. 13 a).

Accordingly, the correction lens portion 111-9 having a plano-convex shape opposite to that of the acoustic lens used in the matching unit 111-3 may be located in front of the rear layer 111-7, and compensates for the refraction phenomenon of light to prevent the light diffusion phenomenon (see fig. 13 b).

In this case, the curvature of the correction lens unit 111-9 may be selectively used according to the final position of the light.

Accordingly, the correction lens unit 111-9 may affect only the focus of light and not the focus of the ultrasonic signal, but the acoustic lens of the matching unit 111-3 may affect the focus of the ultrasonic signal and the focus of light.

The correction lens unit 111-9 may be omitted if necessary, and the focal length of light may be adjusted by changing the correction lens unit 111-9.

Further, the correction lens unit 111-9 may have a confocal function of adjusting the focus of the reflected and received ultrasonic signal and the focus of light at the same time. However, when the correction lens unit 111-9 has a confocal function, the correction lens unit 111-9 needs to be designed to consider the shape of light before passing through the transparent ultrasonic sensor 111.

In this example, the correction lens unit 111-9 includes a single lens, but is not limited thereto, and may include a plurality of lenses by including a lens for aberration correction in addition to a single lens such as a plano-convex lens.

The characteristics of the transparent ultrasonic sensor 111 of this example in which all components (e.g., 111-1 to 111-6, 111-9) located in the effective area AR1 of the transparent ultrasonic sensor 111 having this structure are made of a transparent material that transmits light can be as follows.

First, since the optical impedance matching, that is, the matching is performed by the operation of the matching unit 111-3, the reliability of the signal output from the transparent ultrasonic sensor 111 can be improved.

Further, since the acoustic lens equipped with the focus control function used in the matching unit 111-3 is used, the focus of the light and ultrasonic signals reflected by the object can be adjusted, and thus the light and ultrasonic signals can be focused on the precisely desired position of the piezoelectric portion 111-5. Accordingly, the sharpness of the ultrasonic image obtained by the signal output from the transparent ultrasonic sensor 111 is greatly improved, and thus the precise shape of the object to be detected and the presence or absence of the object can be grasped.

Further, as described above, since the components (e.g., 11 to 16, 19) constituting the transparent ultrasonic sensor 111 are all made of transparent materials such as transparent glass, transparent epoxy, and transparent silicone, the light output from the fiber laser unit 112 can directly pass through the transparent ultrasonic sensor 111 and radiate to the corresponding object.

Accordingly, the arrangement of the optical system including the transparent ultrasonic sensor 111 can be free, and the utilization ratio of the space where the optical system is installed can be improved.

Further, the correction lens unit 111-9 may be selectively used according to user's demand, and the focal length of light may be adjusted by changing the correction lens unit 111-9.

Further, when a plano-concave optical lens coated to 400nm to 1000nm is used as the acoustic lens, light is transmitted well at 400nm to 1000nm, and thus the definition of an ultrasonic image can be improved.

When a plano-concave optical lens is used as the acoustic lens 111-3, a light diffusion shape occurs through the acoustic lens, but the correction lens portion 111-9 supplements the light diffusion shape, and the focal point of light can be adjusted to a desired point. Therefore, the selection range of the acoustic lens can be widened by using the compensation lens.

The shape of light is maintained by the focus adjustment of the acoustic lens 111-3 and the correction lens unit 111-9, so that fine focus can be maintained, and thus a high-resolution optical image (for example, a photoacoustic image or an optical coherence tomographic image) can be obtained.

Further, the first signal line L1 and the second signal line L2 may be connected to the first case 111-7a and the second case 111-7b constituting the case of the transparent ultrasonic sensor 111, respectively, to apply an electric signal to the first electrode 111-5b and the second electrode 111-5c, so that the signal line L1 and the signal line L2 may be easily connected.

Further, by forming the screw thread 111-7b1 or the like in the second housing 111-7b as a housing, connection or coupling with other optical elements can be facilitated. In this way, since the necessary optical element is coupled to the second housing 111-7b located in a portion completely irrelevant to the path of the light emitted from the optical module 100, the light is normally incident on the piezoelectric portion 111-5 of the transparent ultrasonic sensor 111 without damage and passes through the center of the transparent ultrasonic sensor 111 in the normal direction, and thus alignment of the light with the ultrasonic signal can be easily achieved.

Here, the vertical meaning may mean that light propagates in a direction perpendicular to an incident surface of a transparent ultrasonic sensor (e.g., a transparent ultrasonic transducer).

In this way, when light is perpendicularly incident on the ultrasonic sensor, the focal positions of the light and the ultrasonic signal can be precisely matched, and thus the sharpness of an image obtained from the transparent ultrasonic sensor can be further improved.

As described above, a matching layer may be present to minimize the loss of ultrasonic energy in the medium due to the acoustic impedance difference between air and the medium.

There may be one or more matching layers.

In the comparative example, such a matching layer may be formed as follows.

When the medium of the ultrasonic signal is water or biological tissue (15 megarayls), acoustic impedance matching is required for maximum transmission/reception efficiency of ultrasonic energy in the case where the piezoelectric layer is LNO (345 megarayls) or PMN-PT (371 megarayls). In this case, one or more matching layers may be required, ranging from 371 megarayls to 15 megarayls.

In this case, when a particular matching layer is generated using a KLM simulation tool (PiezoCAD, PZFLEX, etc.), it is necessary to find a substance of a suitable matching layer by simulation examining the waveform of an ultrasonic signal transmitted from water or living tissue, and since the thickness of the generated matching layer also affects the ultrasonic waveform, the thickness also affects the waveform to a great extent, it is necessary to find a suitable thickness by adjusting the thickness of the matching layer. Theoretically, the thickness at which the energy loss of the wave is minimum is the minimum loss at λ/4 thickness expected for wave equation (c=λ×f, c: sound velocity about 1480m/s, λ: wavelength, f: expected center frequency).

In conventional ultrasonic sensors, the first matching layer is typically formed from a mixture of silver powder and epoxy (79 mryle). In this case, the acoustic impedance may be adjusted according to the mixing ratio of the silver powder and the epoxy, for example, the silver powder: epoxy resin = 3:125.

Next, a second matching layer may be formed by a parylene (28 megarayl) coating.

When the piezoelectric layer is PVDF or PVDF-TrFE (about 4 megarayls), only the parylene coating may be used to create a matching layer. Here, the matching layer formed of the parylene coating may be used not only as a matching layer but also as protection and insulation against the outside.

However, in the case of the transparent ultrasonic sensor 111 according to the present example, since the components (e.g., 11 to 16, 19) located in the effective area AR1 are transparent, the matching layer 111-3 may be formed using glass in the case of constituting the piezoelectric layer by LNO or PMN-PT. In this case, the raw materials for glass (e.g., borosilicate glass=13 mris, crown glass=142 mris, quartz=145 mris, plate glass=107 mris, sodalime glass=13 mris) are slightly different, and thus a desired glass can be appropriately selected and used.

A second matching layer (e.g., 2 megarayls to 6 megarayls) can then be created using a transparent epoxy or silicone (e.g., PDMS) and a third matching layer can be created using a parylene coating. In this case, the generation of the second matching layer may be omitted, and the second matching layer (e.g., 11) may be formed on the first matching layer (e.g., 13) using a parylene coating. Even in this case, an analog waveform generated by KLM simulation may be used to generate the desired matching layer.

In the transparent ultrasonic sensor 111 according to this example, as an example, an engineering lens made of borosilicate is used as the first matching layer, and the second matching layer is formed on the first matching layer by a parylene coating to perform acoustic impedance matching and protection and signal insulation with respect to the outside.

As described above, the optical lens can perform not only an acoustic impedance matching function but also a function of condensing (i.e., focusing) an ultrasonic signal generated from the piezoelectric layer.

Since the transparent ultrasonic sensor 111 is mainly used for image acquisition, focusing of an ultrasonic signal is a factor greatly affecting high resolution and high sensitivity.

Fig. 14 and 15 are diagrams showing photoacoustic image results obtained by the transparent ultrasonic sensor-based optical ultrasonic integrated catheter apparatus according to the embodiment of the present disclosure.

Referring to fig. 14, it is tested whether a photoacoustic image can be acquired by attaching hair to a 4.0mm hole and inserting a catheter of the transparent ultrasonic sensor-based optical ultrasonic integrated catheter apparatus according to an embodiment of the present disclosure into the 4.0mm hole. As shown, the 3D data obtained by moving and rotating the catheter forward and backward are represented as sectional images, X-Y planes, and the like. The lateral resolution measured with hair was identified as 282um.

Referring to fig. 15, it is tested whether a photoacoustic image can be acquired by rolling and attaching a She Gujia phantom to a 4.5mm hole and inserting a catheter of a transparent ultrasonic sensor-based optical ultrasonic integrated catheter apparatus according to an embodiment of the present disclosure into the 4.0mm hole. As shown, 3D data obtained by moving and rotating the catheter forward and backward are represented as X-Z plane, X-Y plane, etc.

In conventional ultrasonic photoacoustic endoscopes and intravascular catheters using an opaque ultrasonic sensor, it is difficult to position both the optical fiber and the ultrasonic sensor in a limited space, and to synchronize the laser field of view and the ultrasonic field of view at the same time. In addition, various methods such as OCT, fluorescence, and infrared can be used to accurately diagnose intravascular diseases (different conditions observed for each system), but developing a system of limited size is very difficult. As described above, when the transparent ultrasonic sensor according to the present disclosure is used, a limited space can be maximally utilized, and various optical modules can be easily combined. Further, when using an existing ultrasonic sensor, there may be a limit to the use of an optical system existing on an optical path, but when using a transparent ultrasonic sensor, the use of the optical system is free at any position. Furthermore, by coupling with various types of general-purpose optical imaging devices, transparent ultrasonic sensors can provide comprehensive information. In particular, for an endoscope or a catheter, many studies have been made to combine ultrasonic waves and optical images (photoacoustic/OCT/fluorescence/NIRS/NIRF images, etc.). However, since the imaging device needs to be directly inserted into a duct or a blood vessel in the body, the size of the imaging device is very limited. The combination of the transparent ultrasonic sensor and the optical imaging device is optimized to minimize size.

The above-described present disclosure is not limited by the above-described embodiments and drawings, but is limited by the appended claims, and it will be readily understood by those skilled in the art that the configuration of the present disclosure may be variously changed and modified within the scope without departing from the technical spirit of the present disclosure.

Claims

1. An optical ultrasonic integrated endoscope probe based on a transparent ultrasonic sensor, comprising:

a fiber laser unit emitting light;

a transparent ultrasonic sensor disposed between an object to be measured and the fiber laser unit such that light emitted from the fiber laser unit is transmitted through the transparent ultrasonic sensor, the transparent ultrasonic sensor being coaxially aligned with the light emitted from the fiber laser unit, radiating ultrasonic waves to the object, and receiving the reflected ultrasonic waves; and

and an imaging device that acquires an image of the object through the transparent ultrasonic sensor.

2. The transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe of claim 1, further comprising:

an inhalation unit inhaling a preset substance;

a plurality of forceps holes for performing a preset medical function; and

At least one water nozzle for spraying water.

3. The transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe of claim 1, further comprising:

and a reflector changing a path of light from the fiber laser unit to a preset angle.

4. The transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe of claim 1 or 3, further comprising: an optical lens that adjusts a characteristic of light from the fiber laser unit.

5. The transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe according to claim 4, wherein said optical lens is provided in a plurality.

6. The transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe of claim 1, wherein said transparent ultrasonic sensor comprises:

a matching unit that performs optical impedance matching and is made of a transparent material;

a piezoelectric layer located behind the matching unit and made of the transparent material;

a first electrode layer and a second electrode layer each made of a transparent conductive material on the back surface and the front surface of the piezoelectric layer;

a first case connected to the first electrode layer; and

And a second case connected to the second electrode layer.

7. The transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe of claim 6, wherein said matching unit comprises an acoustic lens.

8. The transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe of claim 7, wherein said acoustic lens has a shape of any one of a concave lens, a convex lens and a planar lens.

9. The transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe of claim 6, wherein said matching unit comprises at least one of transparent glass, transparent epoxy and transparent silicone.

10. The transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe of claim 6, wherein said piezoelectric layer of said transparent ultrasonic sensor is a piezoelectric material having optically transparent properties.

11. The transparent ultrasonic sensor-based optical ultrasonic integrated endoscopic probe of claim 10, wherein said piezoelectric layer comprises at least one of LNO, PMN-PT, PVDF, and PVDF-TrFE.

12. The transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe of claim 6, wherein said first electrode layer and said second electrode layer of said transparent ultrasonic sensor are electrodes having optically transparent characteristics.

13. The transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe of claim 12, wherein said first electrode layer and said second electrode layer each comprise at least one of AgNW, ITO, carbon nanotubes, and graphene.

14. The transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe of claim 6, wherein dimensions of said first electrode layer and said second electrode layer are different from one another.

15. The transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe of claim 14, wherein said first housing and said second housing each have an annular shape with an empty space in the center.

16. The transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe of claim 15, wherein said first housing is arranged in contact with an edge portion of said first electrode layer and said second housing is arranged in contact with an edge portion of said second electrode layer.

17. The transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe of claim 16, wherein said piezoelectric layer, said first electrode layer and said first housing are located in an interior space of said second housing.

18. The transparent ultrasonic sensor-based optical ultrasonic integrated endoscopic probe of claim 16, wherein said first housing and said second housing comprise electrically conductive substances.

19. The transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe of claim 16, further comprising:

a first signal line connected to the first housing and a second signal line connected to the second housing.

20. The transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe of claim 15, further comprising:

a rear layer positioned in contact with the first electrode layer and attenuating ultrasonic signals.

21. The transparent ultrasonic sensor-based optical ultrasonic integrated endoscopic probe of claim 20, wherein said rear layer is surrounded by said first housing.

22. The transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe of claim 21, wherein said posterior layer comprises transparent glass or transparent epoxy.

23. The transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe of claim 16, further comprising:

An insulating portion located between the first housings and made of a transparent insulating substance.

24. The transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe of claim 16, further comprising:

and a protective layer which is located in front of the matching unit and performs acoustic impedance matching.

25. The transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe of claim 24, wherein said protective layer comprises parylene.

26. The transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe of claim 16, further comprising:

a correction lens located behind the matching layer, adjusting a focus of light passing through the matching layer, and made of a transparent material.

27. The transparent ultrasonic sensor-based optical ultrasonic integrated endoscope probe of claim 26, wherein said correction lens has a convex shape.

28. An optical ultrasonic integrated endoscope apparatus based on a transparent ultrasonic sensor, comprising:

a probe according to any one of claims 1 to 3 and 6 to 27, which is inserted into a predetermined subject; and

And a front end unit which provides an optical output to the probe through a cable and performs signal processing on an image acquired by the probe.

29. The transparent ultrasonic sensor-based optical ultrasonic integrated endoscopic device of claim 28, wherein said probe further comprises an optical lens that adjusts characteristics of light from said fiber laser unit.

30. The transparent ultrasonic sensor-based optical ultrasonic integrated endoscopic device of claim 29, wherein said optical lenses are provided in a plurality.

31. The transparent ultrasonic sensor-based optical ultrasonic integrated endoscopic device of claim 28, further comprising:

an operation unit connected to the probe through the cable to control movement of the probe,

wherein the operation unit includes:

a knob unit for controlling movement of the probe according to a user's operation;

a suction valve controlling a suction operation of a suction unit installed in the probe;

an air/water valve controlling the operation of a water nozzle device installed in the probe; and

an instrument port controls operation of the medical device through a forceps aperture mounted in the probe.

32. The transparent ultrasonic sensor-based optical ultrasonic integrated endoscopic device of claim 28, further comprising:

a scanning unit connected to the probe through the cable to control a scanning operation of the probe,

wherein the scanning unit includes:

a motor that provides torque to rotate the probe;

a fiber rotating joint unit that provides coaxial alignment between a fiber laser unit connected to the probe that rotates according to the torque of the motor and rotates and a fiber laser unit connected to and fixed to the front end unit; and

a slip ring providing an electrical connection between a signal line connected to the front end unit and fixed and a signal line connected between the probes rotated by the motor and rotated.

33. An optical ultrasound integrated catheter device based on a transparent ultrasound sensor, comprising:

a catheter inserted into a predetermined object; and

a front end unit providing a light output to the catheter via a cable and signal processing the image acquired by the catheter,

wherein the catheter comprises:

a fiber laser unit that emits light from the front end unit; and

A transparent ultrasonic sensor disposed between an object to be measured and the fiber laser unit such that light emitted from the fiber laser unit is transmitted through the transparent ultrasonic sensor, the transparent ultrasonic sensor being coaxially aligned with light emitted from the fiber laser unit, radiating ultrasonic waves to the object, and receiving the reflected ultrasonic waves and transmitting the received reflected ultrasonic waves to the front end unit.

34. The transparent ultrasonic sensor-based optical ultrasonic integrated catheter device of claim 33, further comprising:

35. The transparent ultrasonic sensor-based optical ultrasonic integrated catheter apparatus of claim 33 or 34, wherein the catheter further comprises an optical lens that adjusts the characteristics of light from the fiber laser unit.

36. The transparent ultrasonic sensor-based optical ultrasonic integrated catheter device of claim 35, wherein the optical lens is provided in a plurality.

37. The transparent ultrasonic sensor-based optical ultrasonic integrated catheter device of claim 33, wherein the transparent ultrasonic sensor comprises:

a first case connected to the first electrode layer; and

and a second case connected to the second electrode layer.

38. The transparent ultrasonic sensor-based optical ultrasonic integrated catheter apparatus of claim 37, wherein the matching unit comprises an acoustic lens.

39. The transparent ultrasonic sensor-based optical ultrasonic integrated catheter apparatus of claim 38, wherein the acoustic lens has a shape of any one of a concave lens, a convex lens, and a planar lens.

40. The transparent ultrasonic sensor-based optical ultrasonic integrated catheter apparatus of claim 37, wherein the matching unit comprises at least one of transparent glass, transparent epoxy, and transparent silicone.

41. The transparent ultrasonic sensor-based optical ultrasonic integrated catheter device of claim 37, wherein the piezoelectric layer of the transparent ultrasonic sensor is a piezoelectric material having optically transparent properties.

42. The transparent ultrasonic sensor-based optical ultrasonic integrated catheter device of claim 41, wherein the piezoelectric layer comprises at least one of LNO, PMN-PT, PVDF, and PVDF-TrFE.

43. The transparent ultrasonic sensor-based optical ultrasonic integrated catheter device of claim 37, wherein the first and second electrode layers of the transparent ultrasonic sensor are electrodes having optically transparent characteristics.

44. The transparent ultrasonic sensor-based optical ultrasonic integrated catheter device of claim 43, wherein the first and second electrode layers each comprise at least one of AgNW, ITO, carbon nanotubes, and graphene.

45. The transparent ultrasonic sensor-based optical ultrasonic integrated catheter device of claim 37, wherein the dimensions of the first electrode layer and the second electrode layer are different from each other.

46. The transparent ultrasonic sensor-based optical ultrasonic integrated catheter device of claim 45, wherein the first housing and the second housing each have an annular shape with an empty space in the center.

47. The transparent ultrasonic sensor-based optical ultrasonic integrated catheter device of claim 46, wherein the first housing is arranged in contact with an edge portion of the first electrode layer and the second housing is arranged in contact with an edge portion of the second electrode layer.

48. The transparent ultrasonic sensor-based optical ultrasonic integrated catheter device of claim 47, wherein the piezoelectric layer, the first electrode layer, and the first housing are located in an interior space of the second housing.

49. The transparent ultrasonic sensor-based optical ultrasonic integrated catheter device of claim 47, wherein the first housing and the second housing comprise a conductive substance.

50. The transparent ultrasonic sensor-based optical ultrasonic integrated catheter device of claim 47, further comprising:

51. The transparent ultrasonic sensor-based optical ultrasonic integrated catheter device of claim 46, further comprising:

52. The transparent ultrasonic sensor-based optical ultrasonic integrated catheter device of claim 51, wherein the rear layer is surrounded by the first housing.

53. The transparent ultrasonic sensor-based optical ultrasonic integrated catheter device of claim 52, wherein the rear layer comprises transparent glass or transparent epoxy.

54. The transparent ultrasonic sensor-based optical ultrasonic integrated catheter device of claim 47, further comprising:

55. The transparent ultrasonic sensor-based optical ultrasonic integrated catheter device of claim 47, further comprising:

and a protective layer which is positioned in front of the matching unit and performs acoustic impedance matching.

56. The transparent ultrasonic sensor-based optical ultrasonic integrated catheter device of claim 55, wherein the protective layer comprises parylene.

57. The transparent ultrasonic sensor-based optical ultrasonic integrated catheter device of claim 47, further comprising:

58. The transparent ultrasonic sensor-based optical ultrasonic integrated catheter device of claim 57, wherein the correction lens has a convex shape.

59. The transparent ultrasonic sensor-based optical ultrasonic integrated catheter device of claim 33, further comprising:

an operation unit connected to the catheter through the cable and controlling movement of the catheter,

wherein the operation unit includes:

a knob unit controlling movement of the catheter according to a user's operation;

a suction valve controlling a suction operation of a suction unit installed in the duct;

an air/water valve controlling the operation of a water nozzle device installed in the duct; and

60. The transparent ultrasonic sensor-based optical ultrasonic integrated catheter device of claim 33, further comprising:

a scanning unit connected to the catheter through the cable to control a scanning operation of the catheter,

wherein the scanning unit includes:

a motor that provides torque to rotate the catheter;

a fiber rotating joint unit providing coaxial alignment between a fiber laser unit connected to the catheter rotated according to the torque of the motor and rotated and a fiber laser unit connected and fixed to the front end unit; and

A slip ring providing an electrical connection between a signal line connected to the front end unit and fixed and a signal line connected between the conduits rotated by the motor and rotated.